Flow rate monitor for fluid cooled microwave ablation probe

ABSTRACT

A microwave ablation system includes a generator operable to output energy and an ablation probe coupled to the generator that delivers the energy to a tissue region. The ablation system also includes a controller operable to control the generator and at least one sensor coupled to the ablation probe and the controller that detects an operating parameter of the ablation probe. The controller performs a system check by ramping up an energy output of the generator from a low energy level to a high energy level and monitors an output from the sensor at predetermined intervals of time during the system check to determine an abnormal state. The controller controls the generator to cease the energy output when the controller determines an abnormal state.

CROSS-REFERENCE TO RELATED APPLICATIONS

This patent application is related to copending patent application Ser. No. 12/562,575 filed Sep. 18, 2009 and entitled “METHOD FOR CHECKING HIGH POWER MWA SYSTEM STATUS ON STARTUP”, copending patent application Ser. No. 12/566,299 filed Sep. 24, 2009 and entitled “OPTICAL DETECTION OF INTERRUPTED FLUID FLOW TO MWA ANTENNA”, copending patent application Ser. No. 12/568,972 filed Sep. 29, 2009 and entitled “FLOW RATE MONITOR FOR FLUID COOLED MICROWAVE ABLATION PROBE” and copending patent application Ser. No. 12/569,171 filed Sep. 29, 2009 and entitled “FLOW RATE MONITOR FOR FLUID COOLED MICROWAVE ABLATION PROBE”.

BACKGROUND

1. Technical Field

The present disclosure relates generally to microwave ablation procedures that utilize microwave surgical devices having a microwave antenna which may be inserted directly into tissue for diagnosis and treatment of diseases. More particularly, the present disclosure is directed to a system and method for verifying correct system operation of a microwave ablation system.

2. Background of Related Art

In the treatment of diseases such as cancer, certain types of cancer cells have been found to denature at elevated temperatures (which are slightly lower than temperatures normally injurious to healthy cells.) These types of treatments, known generally as hyperthermia therapy, typically utilize electromagnetic radiation to heat diseased cells to temperatures above 41° C., while maintaining adjacent healthy cells at lower temperatures where irreversible cell destruction will not occur. Other procedures utilizing electromagnetic radiation to heat tissue also include ablation and coagulation of the tissue. Such microwave ablation procedures, e.g., such as those performed for menorrhagia, are typically done to ablate and coagulate the targeted tissue to denature or kill the tissue. Many procedures and types of devices utilizing electromagnetic radiation therapy are known in the art. Such microwave therapy is typically used in the treatment of tissue and organs such as the prostate, heart, liver, lung, kidney, and breast.

One non-invasive procedure generally involves the treatment of tissue (e.g., a tumor) underlying the skin via the use of microwave energy. The microwave energy is able to non-invasively penetrate the skin to reach the underlying tissue. However, this non-invasive procedure may result in the unwanted heating of healthy tissue. Thus, the non-invasive use of microwave energy requires a great deal of control.

Presently, there are several types of microwave probes in use, e.g., monopole, dipole, and helical. One type is a monopole antenna probe, which consists of a single, elongated microwave conductor exposed at the end of the probe. The probe is typically surrounded by a dielectric sleeve. The second type of microwave probe commonly used is a dipole antenna, which consists of a coaxial construction having an inner conductor and an outer conductor with a dielectric junction separating a portion of the inner conductor. The inner conductor may be coupled to a portion corresponding to a first dipole radiating portion, and a portion of the outer conductor may be coupled to a second dipole radiating portion. The dipole radiating portions may be configured such that one radiating portion is located proximally of the dielectric junction, and the other portion is located distally of the dielectric junction. In the monopole and dipole antenna probes, microwave energy generally radiates perpendicularly from the axis of the conductor.

The typical microwave antenna has a long, thin inner conductor that extends along the axis of the probe and is surrounded by a dielectric material and is further surrounded by an outer conductor around the dielectric material such that the outer conductor also extends along the axis of the probe. In another variation of the probe that provides for effective outward radiation of energy or heating, a portion or portions of the outer conductor can be selectively removed. This type of construction is typically referred to as a “leaky waveguide” or “leaky coaxial” antenna. Another variation on the microwave probe involves having the tip formed in a uniform spiral pattern, such as a helix, to provide the necessary configuration for effective radiation. This variation can be used to direct energy in a particular direction, e.g., perpendicular to the axis, in a forward direction (i.e., towards the distal end of the antenna), or combinations thereof.

Invasive procedures and devices have been developed in which a microwave antenna probe may be either inserted directly into a point of treatment via a normal body orifice or percutaneously inserted. Such invasive procedures and devices potentially provide better temperature control of the tissue being treated. Because of the small difference between the temperature required for denaturing malignant cells and the temperature injurious to healthy cells, a known heating pattern and predictable temperature control is important so that heating is confined to the tissue to be treated. For instance, hyperthermia treatment at the threshold temperature of about 41.5° C. generally has little effect on most malignant growth of cells. However, at slightly elevated temperatures above the approximate range of 43° C. to 45° C., thermal damage to most types of normal cells is routinely observed. Accordingly, great care must be taken not to exceed these temperatures in healthy tissue.

In the case of tissue ablation, a high radio frequency electrical current in the range of about 500 MHz to about 10 GHz is applied to a targeted tissue site to create an ablation volume, which may have a particular size and shape. Ablation volume is correlated to antenna design, antenna performance, antenna impedance and tissue impedance. The particular type of tissue ablation procedure may dictate a particular ablation volume in order to achieve a desired surgical outcome. By way of example, and without limitation, a spinal ablation procedure may call for a longer, narrower ablation volume, whereas in a prostate ablation procedure, a more spherical ablation volume may be required.

Microwave ablation devices utilize sensors to determine if the system is working properly. However, without delivery of microwave energy, the sensors may indicate that the probe assembly status is normal. Further, defects in antenna assemblies may not be apparent except at high powers. As such, when microwave ablation system is tested using a low power routine, a post manufacture defect may not be apparent. This is especially important for high power microwave ablation devices, where failures may result in extremely high temperatures and flying debris.

Fluid cooled or dielectrically buffered microwave ablation devices may also be used in ablation procedures to cool the microwave ablation probe. Cooling the ablation probe may enhance the overall ablation pattern of antenna, prevent damage to the antenna and prevent harm to the clinician or patient. However, during operation of the microwave ablation device, if the flow of coolant or buffering fluid is interrupted, the microwave ablation device may exhibit rapid failures due to the heat generated from the increased reflected power.

SUMMARY

The present disclosure provides a microwave ablation system. The microwave ablation system includes a generator operable to output energy, an ablation probe coupled to the generator that is operable to deliver the energy to a tissue region, a controller operable to control the generator, and at least one or more sensors coupled to the ablation probe and the controller. The sensor detects an operating parameter of the ablation probe. The controller performs a system check by ramping up an energy output of the generator from a low energy level to a high energy level and monitors an output from the at least one sensor at predetermined intervals of time during the system check to determine an abnormal state. The controller controls the generator to cease the energy output when the controller determines an abnormal state.

In embodiments, the sensor detects a temperature of the ablation probe, radiating behavior of the ablation probe, fluid pressure, forward and reflective power and fluid flow of coolant.

In yet another embodiment of the microwave ablation system, the sensor is a thermocouple, thermistor, optical fiber, receiving antenna, rectenna, radio frequency power sensor, pressure sensor resistive junction or capacitive junction.

The present disclosure also provides a method of detecting an abnormal state in a microwave ablation system. The method includes the steps of outputting a low energy level from a generator to an ablation probe and detecting an operational parameter of the ablation probe at the low energy level. The detected operational parameter is compared to a predetermined range for the operational parameter and an energy level output of the generator is increased in response to the comparison. The microwave ablation system ceases output of energy from the generator in response to the detected operational parameter being outside the predetermined range.

In embodiments, the operational parameter is a temperature of the ablation probe, radiating behavior of the ablation probe, fluid pressure, forward and reflective power, coolant flow in the probe and insertion depth of probe.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and other aspects, features, and advantages of the present disclosure will become more apparent in light of the following detailed description when taken in conjunction with the accompanying drawings in which:

FIG. 1 shows a representative diagram of a variation of a microwave antenna assembly in accordance with an embodiment of the present disclosure;

FIGS. 2A-2C show graphs of time versus power in accordance with embodiments of the present disclosure;

FIG. 3 shows a system block diagram according to an embodiment of the present disclosure;

FIG. 4 shows a system block diagram according to another embodiment of the present disclosure; and

FIG. 5 shows a flow chart describing a ramping procedure according to an embodiment of the present disclosure.

DETAILED DESCRIPTION

Particular embodiments of the present disclosure are described hereinbelow with reference to the accompanying drawings; however, it is to be understood that the disclosed embodiments are merely exemplary of the disclosure and may be embodied in various forms. Well-known functions or constructions are not described in detail to avoid obscuring the present disclosure in unnecessary detail. Therefore, specific structural and functional details disclosed herein are not to be interpreted as limiting, but merely as a basis for the claims and as a representative basis for teaching one skilled in the art to variously employ the present disclosure in virtually any appropriately detailed structure.

Like reference numerals may refer to similar or identical elements throughout the description of the figures. As shown in the drawings and described throughout the following description, as is traditional when referring to relative positioning on a surgical instrument, the term “proximal” refers to the end of the apparatus which is closer to the user and the term “distal” refers to the end of the apparatus which is further away from the user. The term “clinician” refers to any medical professional (i.e., doctor, surgeon, nurse, or the like) performing a medical procedure involving the use of embodiments described herein.

Electromagnetic energy is generally classified by increasing energy or decreasing wavelength into radio waves, microwaves, infrared, visible light, ultraviolet, X-rays and gamma-rays. As used herein, the term “microwave” generally refers to electromagnetic waves in the frequency range of 300 megahertz (MHz) (3×10⁸ cycles/second) to 300 gigahertz (GHz) (3×10¹¹ cycles/second). As used herein, the term “RF” generally refers to electromagnetic waves having a lower frequency than microwaves. The phrase “ablation procedure” generally refers to any ablation procedure, such as RF or microwave ablation or microwave ablation-assisted resection. The phrase “transmission line” generally refers to any transmission medium that can be used for the propagation of signals from one point to another.

FIG. 1 shows a microwave antenna assembly 100 in accordance with one embodiment of the present disclosure. Antenna assembly 100 includes a radiating portion 12 that is connected by feedline 110 (or shaft) via cable 15 to connector 16, which may further connect the assembly 100 to a power generating source 28, e.g., a microwave or RF electrosurgical generator. Assembly 100, as shown, is a dipole microwave antenna assembly, but other antenna assemblies, e.g., monopole or leaky wave antenna assemblies, may also utilize the principles set forth herein. Distal radiating portion 105 of radiating portion 12 includes a tapered end 120 that terminates at a tip 123 to allow for insertion into tissue with minimal resistance. It is to be understood, however, that tapered end 120 may include other shapes, such as without limitation, a tip 123 that is rounded, flat, square, hexagonal, cylindroconical or any other polygonal shape.

An insulating puck 130 is disposed between distal radiating portion 105 and proximal radiating portion 140. Puck 130 may be formed from any suitable elastomeric or ceramic dielectric material by any suitable process. In some embodiments, the puck 130 is formed by overmolding from polyether block amide (e.g., Pebax® sold by Arkema), polyetherimide (e.g., Ultem® and/or Extern® sold by SABIC Innovative Plastics), polyimide-based polymer (e.g., Vespel® sold by DuPont), or ceramic.

FIG. 2A is a graph depicting an operation of the microwave ablation system according to an embodiment of the invention. As depicted in FIG. 2A, at t=0, the energy output from the generator is 0 W. As t increases, the energy output also increases at a constant slope Δ. Slope Δ is sufficient to prevent any harm to a clinician or patient and to prevent and damage to the system. When t=ramp, with ramp being a value of time sufficient to determine if the microwave ablation system is malfunctioning, the energy output increases to an energy level, e.g., 140 W, sufficient to perform a microwave ablation procedure. During the ramping procedure (0<t<ramp), the microwave ablation system performs a system check to determine if the system is in proper working order or if the system is malfunctioning. If the system is malfunctioning, an energy output from the generator is ceased thereby preventing any harm to a clinician or patient or preventing any further damage to the microwave ablation system.

Alternatively, as shown in FIGS. 2B and 2C, a series of pulses may be used during the start up procedure. As shown in FIG. 2B, the series of pulses have a constant amplitude with a pulse width t_(W). A duty cycle for the pulses may be varied in order to adequately check the system without harming the patient or the clinician. Alternatively, as shown in FIG. 2C, the series of pulses during the start up procedure may have a pulse width T_(W) and vary in amplitude. The amplitude of the pulses may gradually reach an energy level sufficient to perform a microwave ablation procedure.

By utilizing a system check that gradually subjects the device to increasing operational stresses (while monitoring sensor status) will allow for microwave ablation systems to limit the number of devices that are damaged due to operator error, such as not turning on the cooling fluid pump. It will also reduce the likelihood of patient and/or user injury from potentially defective assemblies or from user error.

With reference to FIG. 3, a microwave ablation system, shown generally as 600, according to an embodiment of the disclosure is depicted. System 600 has an antenna assembly 610 that imparts microwave energy to a patient. Antenna assembly 610 is similar to antenna assembly 100 described above or antenna assembly may be a choked wet tip (CWT) antenna because the antenna performance needs cooling for power and tissue matching. Generator 620, which is substantially similar to power generating source 28, is coupled to antenna assembly 610 and provides a source of energy thereto. Controller 630 is coupled to generator 620 and is configured to control generator 620 based on an input or signal from sensor 640. Controller 630 may be a microprocessor or any logic circuit able to receive an input or signal from sensor 640 and provide an output to control generator 620. Sensor 640 may be a thermocouple, thermistor, optical fiber, receiving antenna, rectenna, radio frequency power sensor, pressure sensor resistive junction or capacitive junction. Sensor 640 may be a single sensor or an array of sensors to detect operational parameters of the antenna assembly 610 in order to determine if the microwave ablation system 600 is functioning properly. If the sensor 640 detects an abnormal value or level, the controller 630 controls the generator 620 to cease an energy output. Sensor 640 may be incorporated into antenna assembly 610 or controller 630 or may be coupled to either antenna assembly 610 and/or controller 630. Microwave ablation system 600 may also be incorporated in antenna assembly 610 or may be arranged in two or more devices. For instance, controller 630 and generator 620 may be incorporated in a single device or may be separate devices.

Sensor 640 may be a temperature sensor to detect the temperature of the antenna assembly 610. Temperature sensor may be a thermocouple, thermistor or an optical fiber. A thermocouple is a junction between two different metals that produces a voltage related to a temperature difference. Thermocouples are can also be used to convert heat into electric power. Any circuit made of dissimilar metals will produce a temperature-related difference of voltage. Thermocouples for practical measurement of temperature are made of specific alloys, which in combination have a predictable and repeatable relationship between temperature and voltage. Different alloys are used for different temperature ranges and to resist corrosion. Where the measurement point is far from the measuring instrument, the intermediate connection can be made by extension wires, which are less costly than the materials used to make the sensor. Thermocouples are standardized against a reference temperature of 0 degrees Celsius. Electronic instruments can also compensate for the varying characteristics of the thermocouple to improve the precision and accuracy of measurements.

A thermistor is a type of resistor whose resistance varies with temperature. Thermistors are widely used as inrush current limiters, temperature sensors, self-resetting overcurrent protectors, and self-regulating heating elements. The material used in a thermistor is generally a ceramic or polymer. Thermistors typically achieve a high precision temperature response within a limited temperature range.

Sensor 640 may also be used to monitor radiating behavior, e.g., a receiving antenna or a rectenna. The receiving antenna receives radiation from the antenna assembly and provides an electrical signal to indicate the level of radiation. A rectenna is a rectifying antenna, a special type of antenna that is used to directly convert microwave energy into DC electricity. Its elements are usually arranged in a multi-element phased array with a mesh pattern reflector element to make it directional. A simple rectenna can be constructed from a Schottky diode placed between antenna dipoles. The diode rectifies the current induced in the antenna by the microwaves.

Sensor 640 may also be an RF power sensor that monitors forward and reflected power. The RE power sensor measures the power output of the generator 620 that is utilized by the antenna assembly 610. It can also measure reflected power which is RF energy that is reflected from the ablated tissue region and received by the antenna assembly.

Sensor 640 may also be a pressure sensor for monitoring fluid and/or gas pressure. Pressure sensor generates a signal related to the pressure imposed. Typically, such a signal is electrical, but optical, visual, and auditory signals are also contemplated. Pressure sensors can be classified in terms of pressure ranges they measure, temperature ranges of operation, and most importantly the type of pressure they measure. In terms of pressure type, pressure sensors can be divided into five categories. Absolute pressure sensors which measure the pressure relative to perfect vacuum pressure (0 PSI or no pressure). Gauge pressure sensors may be used in different applications because it can be calibrated to measure the pressure relative to a given atmospheric pressure at a given location. Vacuum pressure sensors are used to measure pressure less than the atmospheric pressure at a given location. Differential pressure sensors measure the difference between two or more pressures introduced as inputs to the sensing unit. Differential pressure sensors may also be used to measure flow or level in pressurized vessels. Sealed pressure sensors are similar to the gauge pressure sensors except that it is previously calibrated by manufacturers to measure pressure relative to sea level pressure.

With reference to FIG. 4, a microwave ablation system, shown generally as 700, according to an embodiment of the present disclosure is depicted. Microwave ablation system 700 may be similar to ablation systems described above with regard to FIGS. 1 and 3. The system 700 includes an ablation device 702 having an antenna 702 a and a handle 702 b used to ablate tissue. Generator 706 supplies the ablation device with energy via coaxial cable 704. Ablation device 702 is supplied with coolant or buffering fluid from coolant supply 710 through conduit 708. The coolant flows through the ablation device 702 as described above and exits the ablation device 702 via conduit 708 into chamber 714. Conduit 708 may be a multi lumen conduit having an inflow lumen for supplying the ablation device 702 with coolant and an outflow lumen for coolant to exit the ablation device 702 into the chamber 714. Additionally, conduit 708 may be provided as two separate conduits, an inflow conduit and an outflow conduit.

As shown in FIG. 4, a sensor 712 is provided to monitor the flow rate through conduit 708. As described above, when coolant circulation is interrupted, the ablation device 702 may tend to exhibit rapid failures. By monitoring the fluid flow, damage to the ablation device 702 as well as harm to the clinician or patient can be prevented. Sensor 712 provides an electrical signal to the controller 716 that represents a real-time fluid flow measurement or pressure measurement. Controller 716 compares the electrical signal to a predetermined range. If the electrical signal is within a predetermined range, the controller 716 signals the generator 706 to continue with the ablation procedure. If the electrical signal is outside the predetermined range, the controller 716 controls the generator 706 to cease the ablation procedure. Sensor 712 may be placed anywhere along the fluid path. For instance, sensor 712 may be placed in antenna 702 a, handle 702 b or along the inflow lumen/conduit or outflow lumen/conduit. The sampling rate of sensor 712 should be sufficient enough to catch intermittent problems with the flow of fluid through the ablation system 700. Sensor 712 may be configured to detect the fluid flow during startup before microwave energy is delivered to the ablation device or during an ablation procedure.

Sensor 712 may be a pressure sensor similar to the pressure sensor described above with regard to FIG. 3. The pressure sensor measures the fluid pressure of the coolant or dielectric buffer and provides an electrical signal to the controller 716.

In some embodiments, sensor 712 may also be a fluid flow meter. There are many different types of fluid flow meters that can be used to measure the flow rate. In a differential pressure flow meter, the flow is calculated by measuring the pressure drop over an obstructions inserted in the flow. The differential pressure flowmeter is based on the Bernoulli's Equation, where the pressure drop and the further measured signal is a function of the square of the flow speed. In a velocity flowmeter the flow is calculated by measuring the speed in one or more points in the flow, and integrating the flow speed over the flow area. In a calorimetric flowmeter, two temperature sensors in close contact with the fluid but thermally insulated from each other are used. One of the two sensors is constantly heated and the cooling effect of the flowing fluid is used to monitor the flowrate. In a stationary (no flow) fluid condition there is a constant temperature difference between the two temperature sensors. When the fluid flow increases, heat energy is drawn from the heated sensor and the temperature difference between the sensors is reduced. The reduction is proportional to the flow rate of the fluid. Response times will vary due the thermal conductivity of the fluid. In general lower thermal conductivity require higher velocity for proper measurement. The calorimetric flowmeter can achieve relatively high accuracy at low flow rates.

An electromagnetic flowmeter operates on Faraday's law of electromagnetic induction that states that a voltage will be induced when a conductor moves through a magnetic field. The liquid serves as the conductor and the magnetic field is created by energized coils outside the flow tube. The voltage produced is directly proportional to the flow rate. Two electrodes mounted in the pipe wall detect the voltage that is measured by a secondary element. Electromagnetic flowmeters can measure difficult and corrosive liquids and slurries, and they can measure flow in both directions with equal accuracy. Electromagnetic flowmeters have a relatively high power consumption and can only be used for electrical conductive fluids such as water.

Ultrasonic flow meters measure the difference of the transit time of ultrasonic pulses propagating in and against flow direction. This time difference is a measure for the average velocity of the fluid along the path of the ultrasonic beam. By using the absolute transit times both the averaged fluid velocity and the speed of sound can be calculated. If a fluid is moving towards a transducer, the frequency of the returning signal will increase. As fluid moves away from a transducer, the frequency of the returning signal decrease. The frequency difference is equal to the reflected frequency minus the originating frequency and can be use to calculate the fluid flow speed.

A positive displacement flowmeter measures process fluid flow by precision-fitted rotors as flow measuring elements. Known and fixed volumes are displaced between the rotors. The rotation of the rotors are proportional to the volume of the fluid being displaced. The number of rotations of the rotor is counted by an integral electronic pulse transmitter and converted to volume and flow rate. The positive displacement rotor construction can be done in several ways: reciprocating piston meters (of single and multiple-piston types); and oval-gear meters having two rotating, oval-shaped gears with synchronized, close fitting teeth. With oval-gear meters, a fixed quantity of liquid passes through the meter for each revolution. Shaft rotation can be monitored to obtain specific flow rates.

With reference to FIG. 5, an operation of the ramping procedure is shown. The procedure starts at step 802 where the microwave ablation system is started. At step 804, t is set to t0 where t is time and t0 is the initial startup time. At step 806, a low energy level is outputted from the generator 28 to the antenna assembly 100. The sensor detects an operational parameter, such as temperature of the ablation probe, radiating behavior of the ablation probe, fluid pressure, forward and reflective power, fluid flow of coolant or insertion depth of probe, of the antenna assembly 100 as described above in step 808. In step 810, the detected operational parameter is compared to a predetermined range of values stored in the controller. The predetermined range of values may be set by a clinician or they may be stored in the controller by a manufacturer of the microwave ablation system. If the detected operational parameter is within the predetermined range, the procedure proceeds to step 812 where a determination is made as to whether t is less than t_(RAMP). If t is less than t_(RAMP), then the procedure proceeds to step 814 where t is increased in predetermined intervals. t can be increased in intervals of N seconds or N minutes where N is any positive integer. In step 816 the energy level output of the generator is increased and step 808, step 810 and step 812 are repeated. When t is no longer less than t_(RAMP), the procedures proceeds to step 820 where the ablation procedure is started and used on a patient. If the controller makes a determination in step 810 that the detected operational parameter in step 808 is not within the predetermined range, the procedure proceeds to step 818 where the controller controls the generator to cease energy output.

The ramping procedure outlined above may avoid an assembly failure and potential clinician or patient injury. Although FIG. 5 depicts a particular arrangement of steps to perform the system check during a ramping procedure, it should be understood that a different arrangement of steps may be used while still falling under the scope of the present disclosure. During the ramping procedure and upon detection of abnormal sensor information, the power ramp would cease and return to zero. The ramp may be made long enough to reliably detect common malfunction mechanisms. Redundant circuit designs or redundant multiple sensor types may provide a form of sensor control.

For instance, if the cooling fluid pump is turned off and no fluid is in the antenna assembly, a pressure sensor may return abnormal pressure levels. As such, a power ramp would cease and the power does not reach a level where the coaxial cable would fail due to lack of cooling. If the antenna assembly is full of cooling fluid but the pump is not running, an abnormal reading from the pressure sensor or a rising temperature from a thermo probe would indicate that cooling of the probe is not sufficient most likely due to lack of flow. Therefore, the power ramp would cease and the power does not reach a level where the coaxial cable would fail due to lack of circulation.

In another example, if the device is not inserted into tissue resulting in a dangerous electromagnetic field pattern, a electromagnetic field detector such as the receiving antenna or rectenna would indicate abnormally high electromagnetic field levels along the shaft or around the handle of the antenna. The detection of the high electromagnetic field levels would prevent an unintended clinician or patient burn.

When the antenna assembly is subjected to high powers, defects may become readily apparent. On ramp up, the sensors indicate abnormal operating conditions thereby preventing the power level from reaching a level sufficient to cause device failure and avoiding clinician or patient injury.

Utilizing a test routine of the ablation probe which gradually subjects the device to increasing operational stresses while monitoring sensor status will allow for MWA systems to limit the number of devices which are damaged due to operator error, such as not turning on the cooling fluid pump. It will also reduce the likely hood likelihood of patient and/or user injury from potentially defective assemblies or from user error. This is especially important for high power microwave ablation devices, where failures may result in extremely high temperatures and flying debris.

The described embodiments of the present disclosure are intended to be illustrative rather than restrictive, and are not intended to represent every embodiment of the present disclosure. Various modifications and variations can be made without departing from the spirit or scope of the disclosure as set forth in the following claims both literally and in equivalents recognized in law. 

What is claimed is:
 1. A microwave ablation system, comprising: a generator operable to output energy; an ablation probe coupled to the generator, the ablation probe operable to deliver energy to tissue; a controller operable to control the generator; a coolant supply fluidly coupled to the ablation probe through a conduit; and a flow rate monitor coupled to the conduit configured to monitor a flow rate of coolant flowing in the conduit, the flow rate monitor comprising at least one flow rate meter selected from the group consisting of an electric flow meter, a velocity flow meter, a calorimetric flow meter, an electromagnetic flow meter, an ultrasonic flow meter, and a positive displacement flow meter, wherein the controller is programmed to perform a system check by ramping up energy output of the generator from a low energy level to a high energy level at a constant rate and monitoring an output from the flow rate monitor at predetermined intervals of time during the system check to determine the existence of an abnormal state, and wherein the controller ceases energy output to the generator when the controller detects an abnormal state.
 2. The microwave ablation system according to claim 1, further comprising at least one sensor coupled to the ablation probe and the controller, the at least one sensor operable to detect an operating parameter of the ablation probe.
 3. The microwave ablation system according to claim 2, wherein the operational parameter is a temperature of the ablation probe.
 4. The microwave ablation system according to claim 3, wherein the at least one sensor is a thermocouple, thermistor, or optical fiber.
 5. The microwave ablation system according to claim 2, wherein the operational parameter is a radiating behavior.
 6. The microwave ablation system according to claim 5, wherein the at least one sensor is a receiving antenna or rectenna.
 7. The microwave ablation system according to claim 2, wherein the operational parameter is forward and/or reflected power.
 8. The microwave ablation system according to claim 7, wherein the at least one sensor is a radio frequency power sensor.
 9. The microwave ablation system according to claim 2, wherein the operational parameter is fluid pressure.
 10. The microwave ablation system according to claim 9, wherein the at least one sensor is a pressure sensor. 